Imaging device

Abstract

According to the imaging device, an inner tube can be detached and drawn out from an outer tube, and the design enables a camera module at the top end of the inner tube to be smoothly separated from a convergent lens; before separation, a convergent lens is arranged at the top end of the outer tube, the object distance of the imaging device can be reduced, contact type imaging is achieved, and images of opaque tissue in the human body can be better obtained. After separation, the camera module can independently complete imaging in conventional transparent gas-phase or liquid-phase media such as air and water without relying on a convergent lens, so that the flexibility of independently using the camera module is reserved, the imaging requirements in different medium environments are further adapted, and two application modes of one visual device, namely, one-lens dual-purpose function, are provided; and the use scene of the equipment is expanded.

Description

Technical Field

[0001] This application relates to the field of medical devices, and in particular to an imaging device. Background Technology

[0002] Imaging devices, as commonly used cavity imaging equipment in the medical field, are widely used in clinical settings. However, existing imaging devices cannot be used both in traditional transparent liquid and transparent gas phases and in opaque tissues. Summary of the Invention

[0003] This application aims to address at least one of the technical problems existing in the prior art. To this end, this application proposes an imaging device that can achieve contact visualization while also accommodating traditional transparent gas phase and transparent liquid phase scenarios.

[0004] An imaging apparatus according to an embodiment of this application includes: outer tube; The inner tube can be inserted inside the outer tube; A camera module is mounted at the top of the inner tube; A light source is disposed on the camera module or the inner tube; A converging lens is disposed at the top of the outer tube.

[0005] In the imaging device of this application embodiment, the inner tube can be detached and extracted from the outer tube. This design allows the camera module at the top of the inner tube to detach smoothly from the converging lens. Before detachment, the top of the outer tube is equipped with a converging lens, which can reduce the object distance of the imaging device and achieve contact imaging to better acquire images of opaque tissues inside the human body. After detachment, the camera module does not need to rely on the converging lens and can independently complete imaging in conventional transparent gaseous or liquid media such as air and water. This retains the flexibility of using the camera module alone and further adapts to the imaging needs of different media environments, providing a "one-lens-dual-use" function for a visual device with two application modes, thus expanding the application scenarios of the device.

[0006] Other features and advantages of this application will be set forth in the following description, and will be apparent in part from the description, or may be learned by practicing this application. Attached Figure Description

[0007] The present application will be further described below with reference to the accompanying drawings and embodiments, wherein: Figure 1 This is a schematic diagram of the structure of the contact-type visual imaging device according to an embodiment of this application; Figure 2 for Figure 1 A magnified view of part A; Figure 3This is a schematic diagram of the tail end of the contact-type visual imaging device according to an embodiment of this application. Figure 4 This is a cross-sectional view of the head of the contact-type visual imaging device according to an embodiment of this application. Figure 5 A schematic diagram of the field of view of the camera module in an existing contact imaging device; Figure 6 A schematic diagram of the object distance for existing imaging devices; Figure 7 This is a schematic diagram of the object distance of the contact-type visual imaging device according to an embodiment of this application; Figure 8 This is a schematic diagram of the emission angle of the light source of the contact-type visual imaging device according to an embodiment of this application; Figure 9 An image showing the imaging effect of an existing imaging device; Figure 10 This is an imaging effect diagram of a contact-type visual imaging device according to an embodiment of this application.

[0008] Icon labels: Outer tube 100; outer tail plug 110; inner tube 200; inner tail plug 210; positive marking 220; sealing lens 230; camera module 300; lens holder 310; lens unit 320; photosensitive component 330; light source 400; converging lens 500. Detailed Implementation

[0009] The embodiments of this application are described in detail below. Examples of the embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar elements or elements having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain this application, and should not be construed as limiting this application.

[0010] In the description of this application, it should be understood that the orientation descriptions, such as up, down, etc., are based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this application.

[0011] In the description of this application, "multiple" refers to two or more. The use of "first" and "second" is for the purpose of distinguishing technical features only and should not be construed as indicating or implying relative importance, or implicitly indicating the number of technical features indicated, or the order in which the technical features are indicated.

[0012] In the description of this application, unless otherwise expressly defined, terms such as "setup," "installation," and "connection" should be interpreted broadly, and those skilled in the art can reasonably determine the specific meaning of the above terms in this application in conjunction with the specific content of the technical solution.

[0013] To better describe the imaging device according to the embodiments of this application, a brief introduction to the application scenarios of the embodiments of this application is provided here. Traditional imaging devices are used in transparent air or water. Due to the requirements of the usage environment, the lens distance must be a certain distance from the object to facilitate space for clinical surgical operations. When it is necessary to use the device in opaque tissues inside the human body to achieve contact visualization, this can be achieved by adding a transparent medium within the object distance range in front of the lens. However, this added transparent medium will cause light refraction, causing the imaging device to lose its function of being used in transparent air or water.

[0014] Meanwhile, the added transparent medium also presents problems: when the imaging device is inside the human body, it is usually rod-shaped to reduce channel occupation and damage, such as in traditional rod-shaped imaging devices. The transparent medium added in front of the lens must also be a matching rod-shaped medium. Although adding this transparent medium enables contact viewing, if the front end of the transparent medium is too far from the lens, the area to be observed will be too small in proportion to the entire image, resulting in poor performance. (See reference...) Figure 5 , Figure 9 It is understood that most of the field of view in the image is used to show the inner wall of the tube or the outer wall of the transparent medium. Therefore, if you want to see it clearly at close range, the transparent medium needs to be shortened, but this often conflicts with the object distance requirements of the imaging device and makes it impossible to achieve a clear image.

[0015] The imaging device of this application differs from existing imaging devices, overcomes the shortcomings of traditional imaging devices, and can be used in both transparent air or water and opaque tissues, while achieving the dual goals of large-scale imaging and clear imaging in contact imaging.

[0016] The imaging device of this application embodiment will be described below based on the above application scenarios.

[0017] refer to Figures 1 to 8 This application discloses an imaging device, which includes: Outer tube 100; The inner tube 200 can be inserted into the outer tube 100; The camera module 300 is located at the top of the inner tube 200; The light source 400 is mounted on the camera module 300 or the inner tube 200; A converging lens 500 is located at the top of the outer tube 100.

[0018] In this embodiment, the inner tube 200 can be detached and extracted from the outer tube 100. This design allows the camera module 300 at the top of the inner tube 200 to detach smoothly from the converging lens 500. Before detachment, the converging lens 500 is provided at the top of the outer tube 100, which can reduce the object distance of the imaging device and realize contact imaging to better acquire images of opaque tissues inside the human body. After detachment, the camera module 300 does not need to rely on the converging lens 500 and can independently complete imaging in conventional transparent gaseous or liquid media such as air and water. This retains the flexibility of using the camera module 300 alone and further adapts to the imaging needs of different media environments, providing a visual device with two application modes, namely the "one lens, two uses" function, which expands the application scenarios of the device.

[0019] After the inner tube 200 is pushed to the top within the outer tube 100, the camera module 300 can maintain a very small distance from the rear end face of the converging lens 500 to obtain a wider field of view.

[0020] The aforementioned converging lens 500 can change the object distance of the imaging device. Specifically, the object distance of the lens unit 320 of the camera module 300 is the first object distance. After adding the converging lens 500, the object distance can be shortened from the first object distance to the second object distance. For example, after the distance is shortened to the second object distance, the object surface can be from the lens unit 320 to the front end surface of the converging lens 500, thereby enabling contact imaging.

[0021] The aforementioned converging lens 500 can be made of optical glass, optical crystals, optical plastics / resins, optical ceramics, etc. Optical glass includes crown glass such as K9 and BK7, flint glass, lanthanum crown glass, etc.; optical crystals include halide crystals such as calcium fluoride (CaF2) and magnesium fluoride (MgF2), quartz crystals (SiO2), sapphire (Al2O3) and other oxide crystals, etc.; optical plastics / resins include polymethyl methacrylate (PMMA), polycarbonate (PC), polystyrene (PS), allyl diethylene glycol carbonate (CR-39), cyclic olefin copolymer resin (COC), etc.

[0022] The inner tube 200 and the outer tube 100 can be separated, so that the camera module 300 installed on the inner tube 200 can be used independently after being detached from the outer tube 100, so as to be suitable for use in traditional transparent liquid phase and transparent gas phase.

[0023] The aforementioned light source 400 can be a light-emitting output terminal including a light-emitting unit and / or a light-conducting component. The light-emitting unit can be one or more of a light-emitting diode (LED) chip, a halogen lamp, or a xenon lamp; the light-conducting component is preferably an optical fiber or fiber bundle, used to conduct the light energy generated by the light-emitting unit to the output terminal. The light source 400 can provide illumination covering the visible light spectrum (wavelengths of approximately 380-780 nm) and specific non-visible light spectra (such as near-infrared light with wavelengths of 780-2500 nm).

[0024] In some implementations, reference Figure 2 , Figure 4 Camera module 300, including: Lens frame 310; Lens unit 320 is disposed on the lens frame 310; The photosensitive component 330 is disposed on the lens holder 310 and located behind the lens unit 320; Wherein, the object distance of the lens unit 320 is a first object distance; the combined object distance of the converging lens 500 and the lens unit 320 is a second object distance that is shortened relative to the first object distance, so that the front end surface of the converging lens 500 is used as the object surface.

[0025] The aforementioned photosensitive component 330 can employ a CCD charge-coupled device or a CMOS complementary metal-oxide-semiconductor sensor, along with the necessary supporting circuitry and structure.

[0026] The aforementioned converging lens 500 can be a convex lens, such as a plano-convex lens or a biconvex lens. It is understood that, while ensuring that the front end face of the converging lens 500 is used as the object surface, there is also the possibility that one end face of the converging lens 500 can be fitted with a concave lens.

[0027] The aforementioned second object distance is the distance between lens unit 320 and the front end surface of converging lens 500, thus making the front end surface of converging lens 500 the object surface, thereby greatly expanding the imaging ratio while maintaining clear imaging, such as... Figure 7 , Figure 10 As shown.

[0028] In this embodiment, the camera module 300 integrates the lens unit 320 and the photosensitive component 330 through the lens holder 310, resulting in a compact structure and stable assembly, ensuring the reliability of basic imaging functions. Simultaneously, it is clearly defined that the object distance when the camera module 300 operates alone is a first object distance, while when combined with the converging lens 500, a second object distance is formed that is shorter than the first object distance. This second object distance is defined as the distance from the lens unit 320 to the front end face of the converging lens 500. After the inner and outer tubes are separated, the camera module uses the first object distance to achieve imaging in transparent air or water, while maintaining sufficient distance between the camera module and tissue to provide space for surgical operations. After the inner and outer tubes are combined, a converging lens is attached to the front of the camera module, using the second object distance to achieve contact imaging capabilities, enabling imaging in opaque tissues and facilitating applications such as visualized puncture.

[0029] In some embodiments, the lens holder 310 has a sealing lens 230 at its front end, which mainly serves to prevent dust and water damage. This facilitates the removal of the inner tube 200 and prevents the camera module 300 from being damaged during use.

[0030] In some embodiments, the outer surface of the outer tube 100 is provided with a scale.

[0031] In this embodiment, a scale is provided on the outer surface of the outer tube 100, which can provide the operator with an intuitive depth reference. When the inner tube 200 is inserted into the outer tube 100 and inserted into the human body, the depth of insertion of the top of the imaging device can be accurately determined by the scale, avoiding tissue damage caused by inaccurate depth control and improving operational safety. At the same time, the scale can also be used to measure the location of the lesion and clarify the size of the lesion, so that doctors can help confirm the condition.

[0032] In some embodiments, the inner tube 200 and / or the outer tube 100 are provided with a positive marking 220.

[0033] In this embodiment, a positive orientation marker 220 is provided on the inner tube 200 and / or the outer tube 100 to visually indicate the correct orientation of the imaging device. When the operator inserts the device into the tissue, they can determine whether the current orientation of the imaging device is correct, ensuring that the operator maintains the correct hand position during operation. This prevents situations where incorrect hand orientation leads to the image acquired by the imaging device moving in a direction inconsistent with, or even opposite to, the operator's expected image movement direction during translation.

[0034] In some embodiments, the outer surface of the outer tube 100 is coated with at least one of the following: an insulating, wear-resistant and protective coating, a hydrophilic coating, a lubricating coating, an antibacterial coating, and an antithrombotic and anticoagulant coating.

[0035] In this embodiment, coating the outer surface of the outer tube 100 with specific functional coatings offers multiple advantages. Insulating, wear-resistant, and protective coatings enhance the wear resistance of the outer tube 100, preventing damage from friction with human tissue and improving electrical safety. Hydrophilic and lubricating coatings reduce frictional resistance between the outer tube 100 and tissue, minimizing discomfort and the risk of tissue damage during insertion. Antibacterial coatings inhibit bacterial growth on the surface of the outer tube 100, reducing the probability of cross-infection. Antithrombotic and anticoagulant coatings prevent blood clotting and adhesion, making them particularly suitable for invasive procedures such as intravascular surgery. These coatings can be selected as needed to specifically optimize the safety, comfort, and applicability of the endoscope, expanding its application value in various clinical scenarios.

[0036] The aforementioned insulating, wear-resistant, and protective coating can be a PTFE Teflon coating or a Pyrene coating.

[0037] The hydrophilic coating can be polyvinylpyrrolidone (PVP), polyacrylamide (PAM), polyvinyl alcohol (PVA), or polyethylene glycol (PEG).

[0038] The aforementioned lubricating coating can be medical-grade silicone oil.

[0039] The antibacterial coating mentioned above can be a nano-silver coating or an anionic antibacterial coating.

[0040] The aforementioned antithrombotic and anticoagulant coating can be a heparin coating.

[0041] In some embodiments, the converging lens 500 is configured with a stepped structure, and the cross-sectional area on the side near the end of the outer tube 100 is smaller than the cross-sectional area on the side near the top of the outer tube 100.

[0042] In this embodiment, the converging lens 500 is configured with a stepped structure, and the cross-sectional area on the side near the end of the outer tube 100 is smaller than that on the side near the top of the outer tube 100. This enhances the assembly stability between the lens and the top of the outer tube 100, prevents displacement or detachment during use, and ensures reliable optical adjustment function. At the same time, the smaller cross-sectional area on the end side reduces the overall size of the endoscope tip, making it easier to insert into a narrow tube cavity and improving the device's adaptability to confined spaces. Furthermore, the larger cross-sectional area on the top side ensures the effective optical area of ​​the lens, ensuring that the focusing effect and imaging quality are not affected.

[0043] In some embodiments, both the outer tube 100 and the inner tube 200 are cylindrical structures, and the converging lens 500 is a cylindrical stepped structure.

[0044] In this embodiment, both the outer tube 100 and the inner tube 200 are cylindrical structures. The cylindrical structure provides a smaller cross-sectional perimeter for the same cross-sectional area, resulting in less tissue channel damage. Its smooth cylindrical surface reduces frictional resistance with human tissue and allows rotation around an axis, reducing tissue irritation and discomfort during insertion and expanding its application range. Simultaneously, it facilitates smooth sliding or disassembly of the inner tube 200 within the outer tube 100, improving operational flexibility. Furthermore, the cylindrical structure is manufactured using mature technology, ensuring the coaxiality of the outer tube 100 and inner tube 200 and preventing assembly deviations from affecting imaging stability. In addition, the converging lens 500 is designed with a cylindrical stepped structure, which fits the cylindrical inner wall of the outer tube 100, enabling tight and stable assembly. The stepped design also ensures an effective light-gathering area and maintains imaging adjustment functionality while controlling the overall lens volume, making the endoscope tip structure more compact.

[0045] In some embodiments, the inner tube 200 is a bendable inner tube 200.

[0046] In this embodiment, the inner tube 200 is designed as a bendable structure, which can flexibly adapt to the curvature of the human tissue space and avoid insertion obstruction or tissue damage caused by bending corners. At the same time, it can also drive the camera module 300 at the top to adjust the observation angle, easily obtain images after bending corners, break through the observation limitations of the traditional rigid inner tube 200, improve the flexibility of operation and the imaging coverage, expand the application range, and ensure more comprehensive and efficient diagnosis and treatment.

[0047] In some embodiments, the outer wall of the inner tube 200 is fitted tightly against the inner wall of the outer tube 100.

[0048] In this embodiment, the outer wall of the inner tube 200 is closely fitted to the inner wall of the outer tube 100, which reduces the gap between them and prevents impurities from entering the gap and affecting the cleanliness of the equipment and the safety of the internal components. At the same time, it also allows the converging lens 500 and the camera module 300 to be better positioned on the designed pipeline. Furthermore, it can improve the stability of the inner tube 200 when sliding or fixed inside the outer tube 100, prevent the inner tube 200 from shaking and causing the imaging of the camera module 300 to shift, and ensure the observation accuracy.

[0049] In some embodiments, the outer tube 100 is provided with an outer end plug 110 at its tail end, and the inner tube 200 is provided with an inner end plug 210 at its tail end. The outer end plug 110 and the inner end plug 210 are detachably connected by a locking structure.

[0050] In this embodiment, the outer tube 100 is provided with an outer end plug 110110 at its tail end and the inner tube 200 is provided with an inner end plug 210210 at its tail end. The two are detachably connected by a locking structure. This can form a sealed protection for the inside of the tube body through the double end plugs, preventing impurities from entering and protecting the precision components. It can also achieve quick disassembly with the help of the detachable locking structure.

[0051] In some embodiments, the outer tail plug 110 is provided with an L-shaped notch, and the inner tail plug 210 is provided with a columnar protrusion structure. The columnar protrusion structure can be rotated and engaged into the L-shaped notch to form a lock, or rotated out of the L-shaped notch to retract.

[0052] In this embodiment, the outer tail plug 110110 is provided with an L-shaped notch and the inner tail plug 210210 is provided with a columnar protrusion. The locking and disengagement can be achieved by rotation. The structure is simple but can quickly complete the fixing and separation of the inner and outer tail plugs 110110, and the operation is convenient and efficient. At the same time, the locking method of rotation and locking is stable and can avoid accidental disengagement during use, which is suitable for the clinical use needs of endoscopes.

[0053] In some embodiments, the radius of curvature of the front end face and the radius of curvature of the rear end face of the converging lens 500 are determined based on the image distance of the camera module 300, the focal length of the lens unit 320, the thickness of the converging lens 500, the refractive index of the converging lens 500, and the inter-lens distance between the lens unit 320 and the rear end face of the converging lens 500.

[0054] In this embodiment, the radius of curvature of the converging lens 500 is precisely calculated based on the position parameters and focal length characteristics of the lens unit 320 and the converging lens 500, enabling the optical parameters of the two to be matched. This shortens the object distance while ensuring clear and stable imaging. This object distance adjustment achieved through the coordinated design of optical parameters eliminates the need for complex mechanical structures, simplifying the device size and improving the practicality and imaging quality for close-up observation. The parts are simple to manufacture and inexpensive.

[0055] In some embodiments, the radius of curvature of the front end face and the radius of curvature of the rear end face of the converging lens 500 are constrained by the following formula: ; Wherein, v is the image distance of the camera module 300, f is the focal length of the lens unit 320, n is the refractive index of the converging lens 500, d is the inter-lens spacing, t is the thickness of the converging lens 500, R1 is the radius of curvature of the front end face of the converging lens 500, and R2 is the radius of curvature of the rear end face of the converging lens 500.

[0056] In this embodiment, this formula can be used to quickly determine the correlation between multiple main parameters that affect optical imaging. Then, based on the pre-determined optical parameters of the camera module 300, the parameter relationship of the converging lens 500 can be clarified, which can guide the quick determination of the optimized or best parameters that can achieve contact imaging, so as to select a suitable converging lens 500.

[0057] In some embodiments, the radius of curvature of the rear end face of the converging lens 500 is greater than or equal to 0.75 mm, the thickness of the converging lens 500 is greater than or equal to 1.8 mm and less than or equal to 20 mm, and the inter-lens spacing is less than or equal to 5.0 mm. Within these ranges, the smaller the thickness of the converging lens 500 and the smaller the inter-lens spacing, the better it is for improving the imaging ratio.

[0058] In this embodiment, the provided value range can be understood as a relatively optimal value range, within which a clearer imaging effect and a larger imaging ratio can be obtained.

[0059] In some embodiments, the radius of curvature of the front end face of the converging lens 500 is greater than or equal to 1.5 mm.

[0060] In this embodiment, the curvature radius of the front end face of the converging lens 500 is further limited, so that the curvature radius of the front end face of the converging lens 500 is appropriately increased, which can reduce the imaging spherical aberration.

[0061] In some implementations, taking K9 glass material with a refractive index of about 1.5 as an example, when d≤5.0mm, the typical values ​​of each parameter can be referred to as the following groups.

[0062] t=1.8, R1=3.0, R2=0.75; t=20, R1=1.5, R2≥100; t=2.1, R1=2.0, R2=1.0; t=6.0, R1=5.5, R2=3.9; t=8.0, R1=8.3, R2=6.3; t=3.5, R1=3.0, R2=1.6; t=10, R1=11, R2=20; All parameters listed above are in mm, and each set can achieve contact imaging. It should be noted that the above parameters are typical reference values; other parameters that meet the formula constraints can also achieve the desired contact imaging effect.

[0063] In some implementations, the rear end face can be replaced by a Fresnel lens surface with an equivalent R2 value, which is equivalent to the spherical surface.

[0064] In some implementations, R1 and R2 can be cemented doublets or aspherical lenses to suppress chromatic aberration / spherical aberration and improve performance.

[0065] In some implementations, R1 and R2 can be replaced by aspherical surfaces to achieve the same effect. When using aspherical surfaces, even-order aspherical surfaces are used, and the general expression is: ; In the formula, Z is the sagitta, r is the coordinate of a point on the surface, C is the mirror curvature, k is the conic coefficient, and A4~A 16 ... represents the coefficients of higher-order terms.

[0066] Specifically, Table 1 provides some feasible parameters for the case where the converging lens 500 has a biconvex structure.

[0067] Table 1

[0068] In some embodiments, the converging lens 500 is also used to reduce reflected light from the lens unit 320 of the camera module 300.

[0069] The aforementioned reduction of the light intensity of the reflected light from the lens unit 320 of the camera module 300, which is reflected by the converging lens 500, can be achieved by directly reducing the light intensity of the reflected light or by causing the reflected light to deviate from the lens unit 320.

[0070] In this embodiment, the performance of the converging lens 500 related to optical reflection is further defined. The converging lens 500 reduces the intensity of reflected light reaching the lens unit 320 of the camera module 300, reducing strong light interference and the likelihood of light spots obscuring image details. It also reduces the image darkening effect caused by strong light spots, resulting in a clearer overall image. Furthermore, the converging lens 500 can guide reflected light away from the lens unit 320, reducing stray light entering the imaging area at its source. This design in this embodiment eliminates the need for additional complex light-shielding structures. While ensuring the camera module 300 receives imaging light normally and maintains the illumination function of the light source 400, it effectively reduces the possibility of light spots, thereby improving image brightness and clarity. This allows operators to more accurately identify subtle lesions within tissues, enhancing diagnostic reliability. Simultaneously, it simplifies the device structure, balancing practicality and ease of operation. For details on the effects of light spots, please refer to the appendix. Figure 9 The image shows strong light spots around the center of the effective field of view, which greatly affects the operator's viewing. The effect after eliminating the light spot effect in this application can be referenced. Figure 10 After the glare is eliminated, the image becomes extremely clear, which is beneficial for observing the target area. In other words, based on the aforementioned function of expanding the field of view, the function of eliminating glare is added to further improve the imaging effect.

[0071] In some implementations, reference Figure 2 , 4 7, 8, The light source 400 includes multiple LED units, which are distributed around the lens unit 320.

[0072] In this embodiment, the light source 400 uses multiple LED units distributed around the edge of the converging lens 500, which allows light to be emitted uniformly from the periphery of the lens and converged by the lens to form a ring illumination around the central imaging area, thereby improving the brightness uniformity of the observation area.

[0073] In some embodiments, the imaging device further includes a light source 400 located around the lens unit 320, the distance from the optical axis of the lens unit 320 to the light source 400 being constrained by the following formula: ; ; Wherein, R2 is the radius of curvature of the rear end face of the converging lens 500, d is the inter-lens spacing, t is the thickness of the converging lens 500, θ is half of the emission angle of the light source 400, α is half of the angle between the incident and reflected rays of the edge rays emitted by the light source 400 at the rear end face of the converging lens 500, and d2 is the distance from the optical axis of the lens unit 320 to the light source 400.

[0074] For an understanding of the parameters mentioned above, please refer to [link / reference]. Figure 8 .

[0075] The emission angle of the light source 400 can be understood as the angle between the light rays at the edge of the illumination range of the light source 400.

[0076] In this embodiment, when R2, d, and θ are given, the distance from the light source 400 to the optical axis of the lens unit 320 of the converging lens 500 used to eliminate the effect of reflection can be obtained by the above formula; or conversely, when d2, d, and θ are given, that is, when the structure limits the distance from the light source 400 to the optical axis of the lens unit 320, the radius of curvature of the rear end face of the converging lens 500 can be guided and determined by the formula.

[0077] In some embodiments, the radius of curvature R1 of the front end face of the converging lens 500 is 70% to 130% of the sum of the thickness of the converging lens 500 and the inter-lens spacing.

[0078] In this embodiment, based on the sum of the thickness of the converging lens 500 and the inter-lens spacing, a suitable range of the radius of curvature of the front end face of the converging lens 500 is determined, which can effectively eliminate the reflection brought by the front end face of the converging lens 500 and further reduce the impact of the light spot.

[0079] It should be noted that when the converging lens 500 comes into contact with opaque tissue, the tissue adheres tightly to the front surface of the converging lens 500 without any gaps, which is equivalent to the tissue being immersed in the medium of the converging lens 500. Therefore, there will be no strong reflective points. However, if there is still a transparent medium on the front surface of the converging lens 500, such as when it comes into contact with opaque brain tissue in the skull, occasional backward movement or local depressions containing water or air on the tissue surface may cause reflection. By following the principle of limiting the radius of curvature of the front surface of the converging lens 500 as described above, the reflective points caused by the front surface of the converging lens 500 can be effectively reduced.

[0080] In some embodiments, the radius of curvature R1 of the front end face of the converging lens 500 is greater than or equal to 1.5 mm.

[0081] In this embodiment, the range of the radius of curvature of the front end face of the converging lens 500 can be understood as a relatively optimal range. Within this range, a relatively ideal effect of reducing the reflective effect of the front end face of the converging lens 500 can be obtained.

[0082] In some embodiments, the inter-lens spacing is less than or equal to 1 mm, and the radius of curvature of the rear end face of the converging lens 500 is less than or equal to 30 mm.

[0083] The inter-scope spacing d is less than or equal to 1 mm. The smaller d is, the lower limit of d2 can be effectively reduced, which is beneficial to reducing the size of the imaging device and thus reducing the damage to tissues during clinical use.

[0084] The radius of curvature R2 of the rear end face of the aforementioned converging lens 500 is less than or equal to 30mm. The smaller R2 is, the lower limit of d2 can be reduced, which is beneficial to reducing the size of the imaging device.

[0085] It should also be noted that the θ angle is half of the emission angle of the light source at 40°. The smaller the θ, the smaller the lower limit of d2 can be, which is beneficial to reducing the size of the imaging device and thus reducing the damage to tissues during clinical use.

[0086] In some implementations, the effect of eliminating light spots is further considered on the basis of contact imaging. Taking the emission angle of light source 400 ≤ 120° as an example, the typical values ​​of each parameter can be referred to as the following groups: With θ = 60°, a launch angle of 120°, and R2 ≤ 30mm, when d = 1.0mm, d2 ≥ 2.0mm; when d = 0.5mm, d2 ≥ 1.10mm; when d = 0.3mm, d2 ≥ 0.7mm; and when d = 0, d2 has no special requirements, only manufacturing needs need to be considered. With θ = 45°, a launch angle of 90°, and R2 ≤ 30mm, when d = 1.0, d2 ≥ 1.15mm; when d = 0.5, d2 ≥ 0.65mm; when d = 0.3mm, d2 ≥ 0.4mm; and when d = 0, d2 has no special requirements, only manufacturing needs need to be considered.

[0087] Each of the above sets of parameters can achieve contact imaging while eliminating light spots. It should be noted that the above sets of parameters are typical reference values; other parameters that meet the formula constraints can also achieve the expected imaging effect.

[0088] In some embodiments, the front and / or rear surfaces of the converging lens 500 are provided with an anti-reflection coating.

[0089] In this embodiment, an anti-reflective coating is provided on the front and / or rear surfaces of the converging lens 500, which can further reduce interference caused by light reflection through the optical properties of the coating. This design, together with the lens structure itself, creates a synergistic anti-reflective effect, further suppressing the generation of light spots without affecting the transmittance of normal imaging light.

[0090] The aforementioned antireflective coatings can be single-layer, double-layer, multi-layer, broadband, or infrared antireflective coatings, prepared using processes such as vacuum evaporation deposition (including electron beam evaporation), sputtering deposition (e.g., magnetron sputtering), ion-assisted deposition (IAD), chemical vapor deposition (CVD), or sol-gel methods. The coating materials include magnesium fluoride (MgF2), silicon dioxide (SiO2), cerium oxide (CeO2), titanium dioxide (TiO2), or combinations thereof. In some implementations, the antireflective coating has a reflectivity of less than 0.5%.

[0091] In this embodiment, the reflectivity of the antireflective coating is controlled to be below 0.5%, which can further reduce the reflected light intensity at the end face of the converging lens 500.

[0092] To better understand the usage of the contact imaging device in the embodiments of this application, a basic usage method is given here, taking the use of intracranial hematoma removal as an example. The method involves first visual puncture, then placement of a tubular brain depressor to provide a surgical pathway, and finally providing a visual full-process visualization of the removal of cerebral hemorrhage within the surgical pathway. The specific process is as follows.

[0093] The contact imaging device of this application embodiment is emitted from the center of the tubular brain retractor and necessary obturator and other accessories; The contact imaging device is inserted into the skull through an opening. During this process, the contact imaging device provides tissue images from the front surface of the converging lens 500. Different tissue types, such as brain tissue and hematoma, produce different images. The images allow for real-time identification of the tissue type at the front surface of the converging lens 500, i.e., the puncture tip. The device continuously assesses the tissue type, avoiding important tissues such as blood vessels to prevent damage, until it reaches the edge of the hematoma. At this point, the first reading is taken using the scale to determine the depth of the hematoma. The device continues to probe downwards in the current direction until the front of the contact imaging device passes through the hematoma area. When the image acquired by the contact imaging device re-contacts the brain tissue from the hematoma, it is confirmed that the device has passed through the hematoma. At this point, a second reading is taken, and the difference between the two readings is the diameter of the hematoma cavity. It should be noted that before the insertion operation begins, the grip direction of the contact imaging device needs to be determined based on the positive marker 220 to ensure correct movement when adjusting the puncture path and avoid misoperation.

[0094] After the hematoma puncture is completed, the tubular brain retractor is pushed into the hematoma along the contact imaging device. Then the contact imaging device is removed, leaving only the tubular brain retractor. The tubular brain retractor is a hollow tube, thus establishing the surgical access to the hematoma cavity. At this point, the inner tube 200 is removed and placed inside the tubular brain retractor, enabling observation of the exposed hematoma tissue in the air. This achieves the second visual function of the imaging device, providing imaging of the hematoma tissue, providing a surgical field of view, and allowing for visual removal of the hematoma using drainage equipment within the field of view.

[0095] In the above process, the contact imaging device of this application embodiment can achieve contact imaging during puncture, and the imaging is free from light spot interference, thus allowing for more accurate access to the hematoma area. At the same time, the scale set on the outer tube 100 can measure the diameter of the hematoma during the insertion process, which is convenient for determining the severity of the accident. This application embodiment adopts a combination of inner tube 200 and outer tube 100. After the combination is used and the tubular brain retractor is placed, the imaging component at the top of the inner tube 200 can be used to directly image and observe the intracranial situation inside the tubular brain retractor, which is convenient for subsequent drainage of the hematoma and realizes full-process visualization of cerebral hemorrhage removal.

[0096] The embodiments of this application have been described in detail above with reference to the accompanying drawings. However, this application is not limited to the above embodiments. Within the scope of knowledge possessed by those skilled in the art, various changes can be made without departing from the spirit of this application.

Claims

1. An image forming apparatus characterized by comprising: The application relates to an endoscope, which comprises an outer tube, an inner tube, a camera module, a light source and a converging lens. The camera module comprises a lens holder, a lens unit and a photosensitive component. The outer surface of the outer tube is provided with a scale. The inner tube and / or the outer tube are provided with a positive identification. The outer surface of the outer tube is coated with at least one of an insulating wear-resistant and protective coating, a hydrophilic coating, a lubricating coating, an antibacterial coating and an antithrombotic and anticoagulant coating. The outer tube and the inner tube are both cylindrical structures.

2. The imaging device of claim 1, wherein, The converging lens is provided in a cylindrical stepped structure, and the cross-sectional area of one side close to the end of the outer tube is smaller than that of one side close to the top of the outer tube. The inner tube is a bendable inner tube. The outer wall of the inner tube is tightly matched with the inner wall of the outer tube. The tail end of the outer tube is provided with an outer tail plug, and the tail end of the inner tube is provided with an inner tail plug. The outer tail plug is provided with an L-shaped notch, and the inner tail plug is provided with a columnar convex structure.

3. The imaging device of claim 1, wherein, The radius of curvature of the front end face and the radius of curvature of the rear end face of the converging lens are determined according to the image distance of the camera module, the focal length of the lens unit, the thickness of the converging lens, the refractive index of the converging lens and the mirror distance between the lens unit and the rear end face of the converging lens.

4. The imaging apparatus according to claim 1, characterized by The radius of curvature of the front end face and the radius of curvature of the rear end face of the converging lens are constrained by the following formula:

5. The imaging device of claim 1, wherein, The radius of curvature of the rear end face of the converging lens is greater than or equal to 0.75 mm, the thickness of the converging lens is greater than or equal to 1.8 mm and less than or equal to 20 mm, the mirror distance is less than or equal to 5.0 mm, and the radius of curvature of the front end face of the converging lens is greater than or equal to 1.5 mm.

6. The imaging apparatus according to claim 1, wherein The converging lens is also used for reducing the reflected light reflected to the lens unit of the camera module by the converging lens.

7. The imaging apparatus according to claim 6, wherein The light source is located around the lens unit, and the distance from the optical axis of the lens unit to the light source is constrained by the following formula:

8. The imaging apparatus of claim 1, wherein, ​ 9. The imaging apparatus of claim 1, wherein, ​ 10. The imaging apparatus according to claim 1, wherein ​ 11. The imaging apparatus according to claim 10, wherein ​ 12. The imaging apparatus of claim 2, wherein, ​ 13. The imaging apparatus of claim 12, wherein, ​ ； ​ 14. The imaging apparatus according to claim 13, wherein ​ 15. The imaging apparatus according to claim 13 or 14, characterized by ​ 16. The imaging apparatus according to claim 2 or 12, wherein ​ ； ； Wherein, R2 is the curvature radius of the rear end face of the converging lens, d is the inter-lens distance between the lens unit and the rear end face of the converging lens, t is the thickness of the converging lens, θ is half of the emission angle of the light source, α is half of the included angle between the incident light and the reflected light of the edge light emitted by the light source at the rear end face of the converging lens, and d2 is the distance from the optical axis of the lens unit to the light source.

17. The imaging apparatus of claim 15, wherein, The curvature radius of the front end face of the converging lens is 70% to 130% of the sum of the thickness of the converging lens and the inter-lens distance; and the curvature radius of the front end face of the converging lens is greater than or equal to 1.5 mm.

18. The imaging apparatus of claim 16, wherein, The inter-lens distance is less than or equal to 1 mm, and the curvature radius of the rear end face of the converging lens is less than or equal to 30 mm.

19. The imaging device of claim 16, wherein, The front end face and / or the rear end face of the converging lens is provided with an anti-reflection film.

Images